US20140275721A1 - Centrifugal Blood Pump With Partitioned Implantable Device - Google Patents
Centrifugal Blood Pump With Partitioned Implantable Device Download PDFInfo
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- US20140275721A1 US20140275721A1 US13/804,144 US201313804144A US2014275721A1 US 20140275721 A1 US20140275721 A1 US 20140275721A1 US 201313804144 A US201313804144 A US 201313804144A US 2014275721 A1 US2014275721 A1 US 2014275721A1
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- Prior art keywords
- motor
- unit
- pumping unit
- motor unit
- substantially planar
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Classifications
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- A61M1/1012—
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/20—Type thereof
- A61M60/205—Non-positive displacement blood pumps
- A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
- A61M60/226—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller the blood flow through the rotating member having mainly radial components
- A61M60/232—Centrifugal pumps
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
- A61M60/178—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart drawing blood from a ventricle and returning the blood to the arterial system via a cannula external to the ventricle, e.g. left or right ventricular assist devices
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/40—Details relating to driving
- A61M60/403—Details relating to driving for non-positive displacement blood pumps
- A61M60/422—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being electromagnetic, e.g. using canned motor pumps
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/80—Constructional details other than related to driving
- A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
- A61M60/871—Energy supply devices; Converters therefor
- A61M60/88—Percutaneous cables
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
- A61M60/148—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel in line with a blood vessel using resection or like techniques, e.g. permanent endovascular heart assist devices
Definitions
- the present invention relates in general to circulatory assist devices, and, more specifically, to an implanted device for a pumping system partitioned into separable pumping and motor units.
- a heart pump system known as a left ventricular assist device (LVAD) can provide long term patient support with an implantable pump associated with an externally-worn pump control unit and batteries.
- the LVAD improves circulation throughout the body by assisting the left side of the heart in pumping blood.
- One such system is the DuraHeart® LVAS system made by Terumo Heart, Inc., of Ann Arbor, Mich.
- the DuraHeart® system employs a centrifugal pump with a magnetically levitated impeller to pump blood from the left ventricle to the aorta.
- An electric motor magnetically coupled to the impeller is driven at a speed appropriate to obtain the desired blood flow through the pump.
- a typical cardiac assist system includes a pumping unit, electrical motor (e.g., a brushless DC motor integrated in the pump housing), drive electronics, microprocessor control unit, and an energy source such as rechargeable batteries and/or an AC power conditioning circuit.
- the system is implanted during a surgical procedure in which a centrifugal pump is placed in the patient's chest.
- An inflow conduit is pierced into the left ventricle to supply blood to the pump.
- One end of an outflow conduit is mechanically fitted to the pump outlet and the other end is surgically attached to the patient's aorta by anastomosis.
- a percutaneous cable connects to the pump, exits the patient through an incision, and connects to the external control unit.
- the goal of the control unit is to autonomously control the pump performance to satisfy the physiologic needs of the patient while maintaining safe and reliable system operation.
- a control system for varying pump speed to achieve a target blood flow based on physiologic conditions is shown in U.S. Pat. No. 7,160,243, issued Jan. 9, 2007, which is incorporated herein by reference in its entirety.
- a target blood flow rate may be established based on the patient's heart rate so that the physiologic demand is met.
- the control unit may establish a speed setpoint for the pump motor to achieve the target blood flow.
- a typical pump motor employed for a blood pump is a three-phase permanent magnet electric motor that can be driven as a brushless DC or a synchronous AC motor without any position sensor.
- the need for a position sensor is avoided by controlling motor operation with one of a variety of methods that use the measured stator phase currents to infer the position.
- Vector control is one typical method used in variable frequency drives to control the torque and speed of a three-phase electric motor by controlling the current fed to the motor phases. This control can be implemented using a fixed or variable voltage drive delivered via an inverter comprised of pulse width modulated H-bridge power switches arranged in phase legs.
- the conventional pumping unit for an implanted system has employed a hermetically sealed housing containing the elements of the pump and motor (i.e., the housing body includes a pumping chamber for containing the impeller and one or more other chambers for containing the motor, magnetic components, and electronics).
- the housing body includes a pumping chamber for containing the impeller and one or more other chambers for containing the motor, magnetic components, and electronics.
- a surgical explantation procedure is performed in which the pumping unit is detached from the inflow and outflow conduits and then removed.
- a replacement unit is then implanted and attached to the existing conduits or conduits the conduits may sometimes also be replaced. It would be desirable to reduce the invasiveness of such surgical replacement procedures.
- the angular separation between the direction in which the outlet extends and the direction in which the cable exits is fixed by the housing design.
- a nominal angle has been chosen that provides an optimal placement for a person having an average physiology.
- structural differences in the physiology of individual patients may present obstructions that could be avoided if the cable exited at an angular separation from the outlet other than at the conventional fixed position.
- a centrifugal blood pump system for implanting into a patient.
- a self-contained pumping unit comprises a pump housing having an inlet, an outlet, and a pump chamber, and an impeller disposed in the pump chamber.
- the inlet extends axially from the pump housing on an inlet side of the pump housing, and the outlet extends radially from the pump housing.
- the pump housing has a substantially planar face opposite from the inlet side.
- a self-contained motor unit comprises a motor housing, a motor stator disposed in the motor housing, and a percutaneous cable passing through a radial exit from the motor housing.
- the motor housing has a substantially planar face configured to mate with the substantially planar face of the pump housing.
- the pumping unit and the motor unit are configured to latch together in a plurality of orientations, each orientation having the substantially planar faces mated and the outlet and radial exit at a different respective angular separation.
- the pumping unit and the motor unit are configured such that after the pumping unit is implanted, the motor unit can be unlatched and a replacement motor unit latched with the pumping unit at the plurality of orientations.
- FIG. 1 is a diagram of a circulatory assist system as one example of an implantable pump employing the present invention.
- FIG. 2 is a perspective view of a prior art centrifugal pump with a fixed angular separation between the outlet and the cable.
- FIG. 3 is a cross section showing one embodiment of a partitioned implantable device with separate pumping and motor units.
- FIG. 4 is a perspective view showing a plurality of orientations between the outlet and the cable exit.
- FIG. 5 is an exploded view showing another embodiment of partitioned pumping and motor units.
- FIG. 6 shows another embodiment of the invention using a clip to attach the partitioned units.
- FIG. 7 shows another embodiment of the invention using a radial collar and pin to attach the partitioned units.
- FIG. 8 shows another embodiment of the invention using a radial collar and buckle to attach the partitioned units.
- a patient 10 is shown in fragmentary front elevational view.
- Surgically implanted either into the patient's abdominal cavity or pericardium 11 is the pumping/motor unit 12 of a ventricular assist device.
- An inflow conduit (on the hidden side of unit 12 ) pierces the heart to convey blood from the patient's left ventricle into pumping unit 12 .
- An outflow conduit 13 conveys blood from pumping unit 12 to the patient's aorta.
- a percutaneous power cable 14 extends from pumping unit 12 outwardly of the patient's body via an incision to a compact control unit 15 worn by patient 10 .
- Control unit 15 is powered by a main battery pack 16 and/or an external AC power supply and an internal backup battery.
- Control unit 15 includes a commutator circuit for driving a motor within pumping unit 12 .
- Control unit 15 monitors for various faults that may occur in pumping/motor unit 12 and generates an alarm whenever a fault is detected that requires correction, by surgical replacement or otherwise.
- FIG. 2 is a perspective view of a prior art pumping/motor unit 20 connected to an inflow conduit 21 .
- Unit 20 has an outlet 22 adapted to be coupled to an outflow conduit or graft 23 .
- An electrical cable 24 exits unit 20 via a cable exit 25 (which may include an electrical connector, not shown).
- the fixed angular separation between outlet 22 and cable exit 25 has been relatively small (e.g., between 0° and 90°).
- surgical placement of both the outflow conduit and the electrical cable can be improved by providing an adjustable angular separation that allows an implantation to best conform to the physiology of the patient.
- FIG. 3 shows a centrifugal pump device 30 having a self-contained pumping/impeller unit 31 and a self-contained motor unit 32 .
- Each self-contained unit is hermetically sealed to preventingress of tissue or fluids other than via an inlet 33 and an outlet 34 in a pump housing 35 of unit 31 .
- Pump housing 35 has a hollow, generally cylindrical or puck shape.
- Inlet 33 extends axially from an inlet side of pump housing 35 .
- Outlet 34 extends from a radial edge of pump housing 35 at a predetermined exit point defined by a volute of a pumping chamber 37 .
- Outlet 34 is typically oriented tangentially at the radial exit point.
- An impeller 36 resides within pumping chamber 37 over a hub 38 .
- Impeller 36 may include upper and lower plates containing embedded magnets ( 40 in the upper plate and 41 in the lower plate) and sandwiched over a plurality of vanes 42 .
- Embedded magnets 40 interact with a levitating magnetic field created by levitation magnets 43 disposed in pump housing 35 .
- Embedded magnet segments 41 in the lower plate of impeller 36 magnetically couple with a rotating magnet field generated in motor unit 32 in order to spin impeller 36 and thereby pump blood out through outlet 34 .
- Motor unit 32 has a motor housing 50 containing a multi-phase motor stator 45 which includes windings 46 and 47 and respective magnetic cores 48 and 49 .
- a stationary stator which couples with the impeller is shown (i.e., wherein impeller 36 is directly driven as a rotor of the stationary stator)
- motor unit 32 can alternatively carry a spinning rotor which carries permanent magnets on the rotor for magnetically driving impeller 36 as known in the art.
- Housings 35 and 50 may be comprised of biocompatible thermoplastics.
- a cable portion 51 on motor unit 32 enters/exits at a radial cable exit feature 52 .
- Electrical conductor 53 connects to windings 46 and 47 to supply electrical power for operating stator 45 .
- An electrical connector (not shown) may be located within radial exit 52 . With or without a connector, radial exit 52 is sealed against ingress of fluids or tissues.
- Pump housing 35 has a substantially planar face 55 on the side opposite from the inlet side.
- Motor housing 50 has a substantially planar face 56 configured to mate with planar face 55 .
- a raised collar 57 extends around the periphery of planar face 56 so that pumping unit 31 and motor unit 32 can be brought together in a nested relationship.
- both planar faces 55 and 56 are circular so that the units can be nested together in any rotated orientation, i.e., with pump outlet 34 and radial cable exit 52 at any radial positions with any desired angular separation.
- planar faces 55 and 56 must be intimately attached according to the desired relative positioning.
- units 31 and 32 are latched together magnetically via an embedded magnet 60 just behind planar face 55 in pump housing 35 and an embedded magnet 61 just behind planar face 56 in motor housing 50 .
- collar 57 prevents any undesirable radial movement of the units.
- the magnetic attraction between magnets 60 and 61 is sufficient to ensure mating of faces 55 and 56 during implantation and use within the patient, but can be manually overcome when desired so that a defective or faulted motor unit can be easily removed during a surgery being conducted to replace it.
- the pump inflow and outflow connections are undisturbed in the event that the failure or defect resides only in the motor unit and not the pumping unit.
- the surgical procedure is much less invasive.
- the cable exit can be positioned in any radial orientation so that the best available placement can be utilized.
- FIG. 4 is a perspective, exploded view showing a self-contained pumping unit 63 attached to the apex of a heart 64 (via an inflow conduit and apical cuff, not shown).
- An outlet 65 can be oriented at any desired radial position during implantation (with a different radial position shown by dashed lines).
- a self-contained motor unit 66 can be mated to pumping unit 63 with a radial cable exit 67 located at any arbitrary radial position. Alternative radial positions of cable exit 67 being shown by dashed lines.
- Units 63 and 66 incorporate a latching mechanism 68 / 69 , e.g., a magnetic latch, that is effective at any rotated position.
- a screw connection or other similar fastener can be used as shown in the next embodiment.
- FIG. 5 shows a pumping unit 70 with an axial inlet 71 and a radial outlet 72 .
- a planar face 73 of unit 70 has a regular, noncircular shape with a plurality of rotational symmetries. In the illustrated embodiment, the shape is octagonal which results in eight different symmetrical positions.
- a motor unit 74 has a radial cable exit 75 and flexible cable 76 for connecting to an external control unit (not shown).
- a planar face 77 is surrounded by a peripheral collar 78 defining a closed, noncircular path having the same rotational symmetries as face 73 .
- face 73 of pumping unit 70 is keyed with collar 78 so that the faces can be mated in one of the plurality of symmetrical orientations.
- Collar 78 prevents both radial (i.e, planar) side-to-side movement and rotational movement between the faces.
- Pumping unit 70 has a threaded fastening hole 80 and motor unit 74 has a fastening hole 81 that are aligned in parallel when faces 73 and 77 are mated.
- a screw 82 has an elongated member 83 with a threaded shaft 84 at one end for entering hole 80 and a flanged portion 85 at the other end for bearing against motor unit 74 .
- FIG. 6 shows an alternative embodiment using a clip.
- a self-contained pumping unit 86 has an inlet 87 and an radial outlet 88 .
- a planar face 89 surrounded by a collar 90 is directed toward a self-contained motor unit 91 .
- a radial cable exit 92 extends from motor unit 91 .
- a planar face 93 is directed toward face 89 and may be surrounded by a ledge 94 that receives collar 90 .
- Collar 90 and ledge 94 define a periphery that is circular or has any other shape that includes a plurality of rotational symmetries. A circular shape is most preferred since it conforms to the shape of the impeller and impeller chamber, and, consequently, provides the smallest size.
- a C-shaped clip 95 having a main webbing 96 extending between a bottom member 97 and a top member 98 .
- Bottom member 97 has an outer ridge 100 for capturing motor unit 91 .
- Top member 98 defines a U-shaped slot 101 between fingers 102 and 103 . Fingers 102 and 103 extend over pumping unit 86 so that outlet 87 is disposed in slot 101 .
- Clip 95 is comprised of a material that is sufficiently flexible to allow members 97 and 98 to spring apart in order to install on or be removed from units 86 and 91 .
- FIG. 7 shows an alternative embodiment wherein a pumping unit 105 has an axial inlet 106 and a radial outlet 108 .
- a semi-circular collar 108 has a groove 110 defined by a lip 11 that extends radially inward. Collar 108 extends for no more than 180° so that it can receive a flange 117 that extending from one side of a motor unit 115 .
- Motor unit 115 has a cable exit 116 and a circumferential groove 188 that defines flange 117 .
- Groove 118 and flange 117 extend completely around motor unit 115 so that flange 117 can be inserted into groove 110 with cable exit 116 in any desired orientation.
- a capture mechanism is comprised of a sliding pin 121 received in a pocket 120 in pumping unit 105 that is placed radially outward from the mated planar faces on the opposite side from the semicircular collar.
- the capture mechanism has a capture member with an cam end 122 with an angled cam surface at one end and a knob 123 at the other end.
- a spring 124 is disposed between pocket 120 and cam end 122 so that end 122 is urged downward.
- FIG. 8 shows a modified embodiment wherein the capture member is comprised of a buckle 130 instead of the sliding pin of FIG. 7 .
- motor unit 115 has a plurality of hooks 133 spaced around its periphery. After inserting flange 117 into groove 110 , one of hooks 133 is lined up with a lever 131 and ring 132 of buckle 130 . The selection of a hook 133 places a cable exit (not shown) at one of a predetermined number of orientations with a respective angular separation between the pump outlet and the cable exit.
Abstract
Description
- Not Applicable.
- Not Applicable.
- The present invention relates in general to circulatory assist devices, and, more specifically, to an implanted device for a pumping system partitioned into separable pumping and motor units.
- Many types of circulatory assist devices are available for either short term or long term support for patients having cardiovascular disease. For example, a heart pump system known as a left ventricular assist device (LVAD) can provide long term patient support with an implantable pump associated with an externally-worn pump control unit and batteries. The LVAD improves circulation throughout the body by assisting the left side of the heart in pumping blood. One such system is the DuraHeart® LVAS system made by Terumo Heart, Inc., of Ann Arbor, Mich. The DuraHeart® system employs a centrifugal pump with a magnetically levitated impeller to pump blood from the left ventricle to the aorta. An electric motor magnetically coupled to the impeller is driven at a speed appropriate to obtain the desired blood flow through the pump.
- A typical cardiac assist system includes a pumping unit, electrical motor (e.g., a brushless DC motor integrated in the pump housing), drive electronics, microprocessor control unit, and an energy source such as rechargeable batteries and/or an AC power conditioning circuit. The system is implanted during a surgical procedure in which a centrifugal pump is placed in the patient's chest. An inflow conduit is pierced into the left ventricle to supply blood to the pump. One end of an outflow conduit is mechanically fitted to the pump outlet and the other end is surgically attached to the patient's aorta by anastomosis. A percutaneous cable connects to the pump, exits the patient through an incision, and connects to the external control unit.
- The goal of the control unit is to autonomously control the pump performance to satisfy the physiologic needs of the patient while maintaining safe and reliable system operation. A control system for varying pump speed to achieve a target blood flow based on physiologic conditions is shown in U.S. Pat. No. 7,160,243, issued Jan. 9, 2007, which is incorporated herein by reference in its entirety. A target blood flow rate may be established based on the patient's heart rate so that the physiologic demand is met. The control unit may establish a speed setpoint for the pump motor to achieve the target blood flow.
- A typical pump motor employed for a blood pump is a three-phase permanent magnet electric motor that can be driven as a brushless DC or a synchronous AC motor without any position sensor. The need for a position sensor is avoided by controlling motor operation with one of a variety of methods that use the measured stator phase currents to infer the position. Vector control is one typical method used in variable frequency drives to control the torque and speed of a three-phase electric motor by controlling the current fed to the motor phases. This control can be implemented using a fixed or variable voltage drive delivered via an inverter comprised of pulse width modulated H-bridge power switches arranged in phase legs.
- Reliability, fault detection, and fault tolerance are important characteristics of an electrically-powered blood pump, drive system, and cable. Co-pending application U.S. Ser. No. 13/418,447, filed Mar. 13, 2012, entitled “Fault Monitor For Fault Tolerant Implantable Pump,” which is hereby incorporated by reference, discloses a fault-tolerant inverter/cable system wherein redundant inverter legs are coupled to the motor phases by redundant, parallel conductors between the external unit and the implanted pump. For a three-phase motor, the redundant interconnect system includes six conductors in the cable. By monitoring the equality of the current and/or voltage of the two conductors on the same phase, a fault or impending fault can be detected for each individual conductor. Co-pending application U.S. Ser. No. 13/742,469, filed Jan. 16, 2013, entitled “Motor Fault Monitor for Implantable Blood Pump,” which is hereby incorporated by reference, discloses technology for detecting other pump failures such as a soldering terminal failure, a coil wire breakage, damage to a flex circuit substrate, a coil turn-to-turn short, a layer-to-layer short, and a core/yoke detachment.
- The conventional pumping unit for an implanted system has employed a hermetically sealed housing containing the elements of the pump and motor (i.e., the housing body includes a pumping chamber for containing the impeller and one or more other chambers for containing the motor, magnetic components, and electronics). In the event of a fault associated with any one of the pumping chamber, impeller, motor, magnetic components, or electronics that is serious enough to require replacement, then a surgical explantation procedure is performed in which the pumping unit is detached from the inflow and outflow conduits and then removed. A replacement unit is then implanted and attached to the existing conduits or conduits the conduits may sometimes also be replaced. It would be desirable to reduce the invasiveness of such surgical replacement procedures.
- With an integrated housing containing an inlet and an outlet for the pumping chamber and a connector/cable exit, the angular separation between the direction in which the outlet extends and the direction in which the cable exits is fixed by the housing design. A nominal angle has been chosen that provides an optimal placement for a person having an average physiology. However, structural differences in the physiology of individual patients may present obstructions that could be avoided if the cable exited at an angular separation from the outlet other than at the conventional fixed position.
- In one aspect of the invention, a centrifugal blood pump system is provided for implanting into a patient. A self-contained pumping unit comprises a pump housing having an inlet, an outlet, and a pump chamber, and an impeller disposed in the pump chamber. The inlet extends axially from the pump housing on an inlet side of the pump housing, and the outlet extends radially from the pump housing. The pump housing has a substantially planar face opposite from the inlet side. A self-contained motor unit comprises a motor housing, a motor stator disposed in the motor housing, and a percutaneous cable passing through a radial exit from the motor housing. The motor housing has a substantially planar face configured to mate with the substantially planar face of the pump housing. The pumping unit and the motor unit are configured to latch together in a plurality of orientations, each orientation having the substantially planar faces mated and the outlet and radial exit at a different respective angular separation. The pumping unit and the motor unit are configured such that after the pumping unit is implanted, the motor unit can be unlatched and a replacement motor unit latched with the pumping unit at the plurality of orientations.
-
FIG. 1 is a diagram of a circulatory assist system as one example of an implantable pump employing the present invention. -
FIG. 2 is a perspective view of a prior art centrifugal pump with a fixed angular separation between the outlet and the cable. -
FIG. 3 is a cross section showing one embodiment of a partitioned implantable device with separate pumping and motor units. -
FIG. 4 is a perspective view showing a plurality of orientations between the outlet and the cable exit. -
FIG. 5 is an exploded view showing another embodiment of partitioned pumping and motor units. -
FIG. 6 shows another embodiment of the invention using a clip to attach the partitioned units. -
FIG. 7 shows another embodiment of the invention using a radial collar and pin to attach the partitioned units. -
FIG. 8 shows another embodiment of the invention using a radial collar and buckle to attach the partitioned units. - Referring to
FIG. 1 , apatient 10 is shown in fragmentary front elevational view. Surgically implanted either into the patient's abdominal cavity orpericardium 11 is the pumping/motor unit 12 of a ventricular assist device. An inflow conduit (on the hidden side of unit 12) pierces the heart to convey blood from the patient's left ventricle intopumping unit 12. An outflow conduit 13 conveys blood from pumpingunit 12 to the patient's aorta. Apercutaneous power cable 14 extends frompumping unit 12 outwardly of the patient's body via an incision to acompact control unit 15 worn bypatient 10.Control unit 15 is powered by amain battery pack 16 and/or an external AC power supply and an internal backup battery.Control unit 15 includes a commutator circuit for driving a motor within pumpingunit 12.Control unit 15 monitors for various faults that may occur in pumping/motor unit 12 and generates an alarm whenever a fault is detected that requires correction, by surgical replacement or otherwise. -
FIG. 2 is a perspective view of a prior art pumping/motor unit 20 connected to aninflow conduit 21.Unit 20 has an outlet 22 adapted to be coupled to an outflow conduit orgraft 23. Anelectrical cable 24exits unit 20 via a cable exit 25 (which may include an electrical connector, not shown). In a typical integrated pump and motor housing, the fixed angular separation between outlet 22 andcable exit 25 has been relatively small (e.g., between 0° and 90°). In one aspect of the invention, surgical placement of both the outflow conduit and the electrical cable can be improved by providing an adjustable angular separation that allows an implantation to best conform to the physiology of the patient. -
FIG. 3 shows acentrifugal pump device 30 having a self-contained pumping/impeller unit 31 and a self-containedmotor unit 32. Each self-contained unit is hermetically sealed to preventingress of tissue or fluids other than via aninlet 33 and anoutlet 34 in apump housing 35 ofunit 31.Pump housing 35 has a hollow, generally cylindrical or puck shape.Inlet 33 extends axially from an inlet side ofpump housing 35.Outlet 34 extends from a radial edge ofpump housing 35 at a predetermined exit point defined by a volute of apumping chamber 37.Outlet 34 is typically oriented tangentially at the radial exit point. Animpeller 36 resides within pumpingchamber 37 over ahub 38.Impeller 36 may include upper and lower plates containing embedded magnets (40 in the upper plate and 41 in the lower plate) and sandwiched over a plurality ofvanes 42. Embeddedmagnets 40 interact with a levitating magnetic field created bylevitation magnets 43 disposed inpump housing 35. Embeddedmagnet segments 41 in the lower plate ofimpeller 36 magnetically couple with a rotating magnet field generated inmotor unit 32 in order to spinimpeller 36 and thereby pump blood out throughoutlet 34. -
Motor unit 32 has amotor housing 50 containing amulti-phase motor stator 45 which includeswindings magnetic cores impeller 36 is directly driven as a rotor of the stationary stator),motor unit 32 can alternatively carry a spinning rotor which carries permanent magnets on the rotor for magnetically drivingimpeller 36 as known in the art.Housings - A
cable portion 51 onmotor unit 32 enters/exits at a radialcable exit feature 52.Electrical conductor 53 connects to windings 46 and 47 to supply electrical power for operatingstator 45. An electrical connector (not shown) may be located withinradial exit 52. With or without a connector,radial exit 52 is sealed against ingress of fluids or tissues. -
Pump housing 35 has a substantiallyplanar face 55 on the side opposite from the inlet side.Motor housing 50 has a substantiallyplanar face 56 configured to mate withplanar face 55. A raisedcollar 57 extends around the periphery ofplanar face 56 so that pumpingunit 31 andmotor unit 32 can be brought together in a nested relationship. Preferably, both planar faces 55 and 56 are circular so that the units can be nested together in any rotated orientation, i.e., withpump outlet 34 andradial cable exit 52 at any radial positions with any desired angular separation. - To ensure proper control of the rotation of
impeller 36, planar faces 55 and 56 must be intimately attached according to the desired relative positioning. In the embodiment shown inFIG. 3 ,units magnet 60 just behindplanar face 55 inpump housing 35 and an embeddedmagnet 61 just behindplanar face 56 inmotor housing 50. Withunits collar 57 prevents any undesirable radial movement of the units. The magnetic attraction betweenmagnets faces -
FIG. 4 is a perspective, exploded view showing a self-containedpumping unit 63 attached to the apex of a heart 64 (via an inflow conduit and apical cuff, not shown). Anoutlet 65 can be oriented at any desired radial position during implantation (with a different radial position shown by dashed lines). A self-containedmotor unit 66 can be mated to pumpingunit 63 with aradial cable exit 67 located at any arbitrary radial position. Alternative radial positions ofcable exit 67 being shown by dashed lines.Units latching mechanism 68/69, e.g., a magnetic latch, that is effective at any rotated position. As an alternative to a magnetic latch, a screw connection or other similar fastener can be used as shown in the next embodiment. -
FIG. 5 shows apumping unit 70 with anaxial inlet 71 and aradial outlet 72. Aplanar face 73 ofunit 70 has a regular, noncircular shape with a plurality of rotational symmetries. In the illustrated embodiment, the shape is octagonal which results in eight different symmetrical positions. Amotor unit 74 has aradial cable exit 75 andflexible cable 76 for connecting to an external control unit (not shown). Aplanar face 77 is surrounded by aperipheral collar 78 defining a closed, noncircular path having the same rotational symmetries asface 73. Thus, face 73 of pumpingunit 70 is keyed withcollar 78 so that the faces can be mated in one of the plurality of symmetrical orientations.Collar 78 prevents both radial (i.e, planar) side-to-side movement and rotational movement between the faces. Pumpingunit 70 has a threadedfastening hole 80 andmotor unit 74 has afastening hole 81 that are aligned in parallel when faces 73 and 77 are mated. Ascrew 82 has an elongatedmember 83 with a threadedshaft 84 at one end for enteringhole 80 and aflanged portion 85 at the other end for bearing againstmotor unit 74. -
FIG. 6 shows an alternative embodiment using a clip. A self-containedpumping unit 86 has aninlet 87 and anradial outlet 88. Aplanar face 89 surrounded by acollar 90 is directed toward a self-containedmotor unit 91. Aradial cable exit 92 extends frommotor unit 91. Aplanar face 93 is directed towardface 89 and may be surrounded by aledge 94 that receivescollar 90.Collar 90 andledge 94 define a periphery that is circular or has any other shape that includes a plurality of rotational symmetries. A circular shape is most preferred since it conforms to the shape of the impeller and impeller chamber, and, consequently, provides the smallest size. After faces 89 and 93 are brought together with any desired angular separation betweenoutlet 88 andcable exit 92, they are held together by a C-shapedclip 95 having amain webbing 96 extending between abottom member 97 and atop member 98.Bottom member 97 has anouter ridge 100 for capturingmotor unit 91.Top member 98 defines aU-shaped slot 101 betweenfingers Fingers pumping unit 86 so thatoutlet 87 is disposed inslot 101.Clip 95 is comprised of a material that is sufficiently flexible to allowmembers units -
FIG. 7 shows an alternative embodiment wherein apumping unit 105 has anaxial inlet 106 and aradial outlet 108. Asemi-circular collar 108 has agroove 110 defined by alip 11 that extends radially inward.Collar 108 extends for no more than 180° so that it can receive aflange 117 that extending from one side of amotor unit 115.Motor unit 115 has acable exit 116 and a circumferential groove 188 that definesflange 117. Groove 118 andflange 117 extend completely aroundmotor unit 115 so thatflange 117 can be inserted intogroove 110 withcable exit 116 in any desired orientation. -
Flange 117 slides radially intogroove 110. A capture mechanism is comprised of a slidingpin 121 received in apocket 120 in pumpingunit 105 that is placed radially outward from the mated planar faces on the opposite side from the semicircular collar. The capture mechanism has a capture member with ancam end 122 with an angled cam surface at one end and aknob 123 at the other end. Aspring 124 is disposed betweenpocket 120 and cam end 122 so thatend 122 is urged downward. When flange 117 is being slid intogroove 110,motor unit 115forces cam end 122 into the pocket againstspring 124. Onceflange 117 fully entersgroove 110 thencam end 122 extends downward so thatmotor unit 115 is captured on pumpingunit 105 with their planar faces securely fastened until a manual pull onknob 123 releases them. -
FIG. 8 shows a modified embodiment wherein the capture member is comprised of abuckle 130 instead of the sliding pin ofFIG. 7 . Thus,motor unit 115 has a plurality ofhooks 133 spaced around its periphery. After insertingflange 117 intogroove 110, one ofhooks 133 is lined up with alever 131 andring 132 ofbuckle 130. The selection of ahook 133 places a cable exit (not shown) at one of a predetermined number of orientations with a respective angular separation between the pump outlet and the cable exit.
Claims (10)
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US13/804,144 US20140275721A1 (en) | 2013-03-14 | 2013-03-14 | Centrifugal Blood Pump With Partitioned Implantable Device |
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US13/804,144 US20140275721A1 (en) | 2013-03-14 | 2013-03-14 | Centrifugal Blood Pump With Partitioned Implantable Device |
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US13/804,144 Abandoned US20140275721A1 (en) | 2013-03-14 | 2013-03-14 | Centrifugal Blood Pump With Partitioned Implantable Device |
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